JPWO2013115005A1 - Ultrasonic diagnostic equipment - Google Patents

Abstract

An ultrasonic diagnostic apparatus includes an ultrasonic probe having a capacitive ultrasonic transducer, a transmission circuit that receives the ultrasonic probe in a detachable manner, and generates an ultrasonic transmission signal and a reception circuit. A capacitive ultrasonic transducer, receiving a transmission ultrasonic transducer composed of a plurality of transmission capacitive cells that transmit ultrasonic waves and a reflected ultrasonic wave of the transmitted ultrasonic waves An ultrasonic transducer for reception composed of a plurality of reception capacitive cells that output ultrasonic reception signals, a transmission signal cable for connecting between the ultrasonic transducer for transmission and the transmission circuit, and reception A reception signal cable connecting between the ultrasonic transducer for reception and the reception circuit, and first and second matching units for matching electrical impedance with respect to the ultrasonic transmission signal and the ultrasonic reception signal, respectively. .

Description

  The present invention relates to an ultrasonic diagnostic apparatus that performs ultrasonic diagnosis using a capacitive ultrasonic transducer.

In recent years, development of ultrasonic equipment using a capacitive vibrator (abbreviated as C-MUT) different from a piezoelectric vibrator for an ultrasonic vibrator has been promoted.
C-MUT provides a vacuum space region between the upper and lower electrodes, and sends the ultrasonic waves to the inspection target site by applying a DC bias voltage and a transmission signal or ultrasonic transmission signal to the upper electrode, and reflects it. The ultrasonic wave that is returned is received by the upper membrane and converted into an ultrasonic echo signal (also referred to as an ultrasonic reception signal or simply a reception signal) as a converted electrical signal. To do.
A problem is that the transmission signal to the C-MUT and the reception signal received by the C-MUT are transmitted by the cable, and impedance mismatch occurs between the cable and the transmission / reception sensitivity due to the capacitance of the C-MUT. There is.

Specifically, due to impedance mismatch, the waveform of the transmission signal is distorted due to reflection of the transmission signal, the level of the transmission signal that can be actually applied to the C-MUT is reduced, or the received signal is not received. Waveforms resulting from matching are superimposed, so that reception sensitivity is lowered and S / N is lowered.
With respect to such a phenomenon, in the conventional example of Japanese Patent No. 4575372, in order to prevent a decrease in reception sensitivity, the output is low in the vicinity of the transducer element so as to electrically match the impedance of the cable. It is specified that an impedance conversion means for converting to impedance is provided.

In the above conventional example, both transmission and reception are configured by the same path, and in particular, impedance conversion means is provided by paying attention to the received signal output. However, in the C-MUT, the vibration characteristics of the upper film are different between transmission and reception, and as a result, there may be a difference in the impedance characteristics of the C-MUT. Therefore, it is difficult to make the best use of the characteristics of the C-MUT even if impedance matching is performed only on the received signal by the impedance conversion means as in the conventional example.
The present invention has been made in view of the above-described points. When performing transmission / reception of ultrasonic waves by a capacitive vibrator (C-MUT), impedance matching is performed at both transmission and reception, and reception is performed. An object of the present invention is to provide an ultrasonic diagnostic apparatus capable of acquiring an ultrasonic image with good sensitivity and S / N.

  An ultrasonic diagnostic apparatus according to one embodiment of the present invention includes an ultrasonic probe having a capacitive ultrasonic transducer, and the ultrasonic probe is detachably connected to the ultrasonic transducer from the capacitive ultrasonic transducer. An ultrasonic wave having a transmission circuit that generates an ultrasonic transmission signal for transmitting the ultrasonic wave, and a reception circuit that performs signal processing on the ultrasonic wave reception signal generated by receiving the ultrasonic wave by the capacitive ultrasonic transducer An ultrasonic transducer for transmission composed of an observation device, a plurality of transmission capacitive cells that transmit the ultrasonic waves, and the reflected ultrasonic wave of the transmitted ultrasonic waves Receiving ultrasonic transducers composed of a plurality of reception capacitive cells that receive ultrasonic waves and output ultrasonic reception signals, and between the transmission ultrasonic transducer and the transmission circuit of the ultrasonic observation device A transmission signal cable for connecting the It is transmitted by the reception signal cable connecting the trusted ultrasonic transducer and the reception circuit of the ultrasonic observation apparatus, and the ultrasonic transmission signal and the reception signal cable transmitted by the transmission signal cable. First and second matching units for matching electrical impedance with respect to the ultrasonic reception signal, respectively.

FIG. 1 is a diagram showing an overall configuration of an ultrasonic diagnostic apparatus according to a first embodiment of the present invention. FIG. 2 is a block diagram showing a configuration of a circuit system for transmitting and receiving ultrasonic waves in FIG. FIG. 3 is a circuit diagram showing a specific circuit of the matching element. FIG. 4 is a block diagram showing a configuration of a circuit system that transmits and receives ultrasonic waves according to a modification of the first embodiment. FIG. 5 is a diagram showing an outline of the configuration of an ultrasonic diagnostic apparatus according to the second embodiment of the present invention. FIG. 6 is a diagram showing an outline of the configuration of an ultrasonic diagnostic apparatus according to the third embodiment of the present invention. FIG. 7 is a diagram showing the configuration of an electronic scanning ultrasonic diagnostic apparatus according to the present invention. FIG. 8 is a diagram illustrating timing of a selection signal and the like generated from the selection control signal of FIG. FIG. 9 is a diagram showing a configuration of a transmission ultrasonic transducer and a peripheral portion of a reception ultrasonic transducer configured to perform impedance matching for each transmission and reception capacitive cell used for ultrasonic transmission / reception. FIG. 10 is a timing chart when the rotation angle of the stepping motor is synchronized with an ultrasonic transmission / reception period of one pixel in the first embodiment.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.
(First embodiment)
As shown in FIG. 1, in the ultrasonic diagnostic apparatus 1 according to the first embodiment of the present invention, an ultrasonic endoscope 2 and an ultrasonic connector 7 of the ultrasonic endoscope 2 are detachably attached (connected). An ultrasonic observation apparatus (hereinafter simply abbreviated as an observation apparatus) 3, a first monitor 4 that displays an ultrasonic tomographic image generated by the observation apparatus 3, and an endoscope connector of the ultrasonic endoscope 2 An endoscope processor 5 to which 8 is detachably attached (connected), and a second monitor 6 that displays an endoscope image generated by the endoscope processor 5 are provided.
The ultrasonic endoscope 2 includes an insertion portion 11 to be inserted into a body cavity, an operation portion 12 provided at the rear end of the insertion portion 11, an ultrasonic cable 13 extending from the operation portion 12, and an endoscope. Cable 14. An ultrasonic connector 7 is provided at the end of the ultrasonic cable 13, and an endoscope connector 8 is provided at the end of the endoscope cable 14.

A capacitive ultrasonic transducer (C-MUT) 16 is disposed in the distal end portion 15 of the insertion portion 11 to transmit (transmit) ultrasonic waves and receive ultrasonic waves that are reflected back from the transmitted ultrasonic waves. The C-MUT 16 is attached to the distal end of the rotating shaft 19 inserted through the insertion portion 11 via the vibrator mounting base 20.
In the present embodiment, the C-MUT 16 transmits a plurality of (in this case, four) transmission capacitive ultrasonic transducer cells (hereinafter referred to as transmission capacitive cells) that transmit ultrasonic waves by application of ultrasonic transmission signals. ) 17a-17d transmitting ultrasonic transducers 17 and a plurality (four in this case) of receiving capacitive ultrasonic transducer cells that receive reflected ultrasonic waves and output ultrasonic reception signals (Hereinafter referred to as receiving capacitance type cells) 18a to 18d.

The reception ultrasonic transducer 18 receives the ultrasonic wave transmitted from the transmission ultrasonic transducer 17 and reflected by the inspection target site, so that the transmission ultrasonic transducer 17 and the reception ultrasonic vibration are received. The child 18 is desirably arranged within a small distance. In FIG. 1, the transmitting ultrasonic transducer 17 and the receiving ultrasonic transducer 18 are formed as adjacent to each other at the tip portion 15 as a predetermined transmission region. The C-MUT cell region for transmission (abbreviated as cell region for transmission) Rs and the C-MUT cell region for reception (abbreviated as cell region for reception) Rr as predetermined reception regions are arranged.
In the present embodiment, the transmission cell region Rs in which the four transmission capacitance type cells 17a to 17d are arranged is obtained when, for example, an ultrasonic image for one frame in radial scanning is acquired as described below. In each transmission period, it becomes a predetermined transmission area for transmitting an ultrasonic wave for generating an ultrasonic beam for one pixel. In other words, four transmission capacitive cells 17a-17d are provided in the transmission cell region Rs, which is a predetermined transmission region set as a transmission region for transmitting an ultrasonic wave for generating an ultrasonic beam for one pixel. Has been placed.

In addition, the reception cell region Rr in which the four reception capacitive cells 18a to 18d are arranged has an ultrasonic wave for one pixel in each reception period when acquiring an ultrasonic image for one frame in radial scanning. This is a predetermined reception area for receiving ultrasonic waves for acquiring a beam. In other words, in order to acquire an ultrasonic beam for one pixel, reflected ultrasonic waves (reflected signals) of ultrasonic waves transmitted from the four transmission capacitive cells 17a-17d arranged in the transmission cell region Rs. The four receiving capacitance type cells 18a to 18d are arranged in a receiving cell region Rr which is a predetermined receiving region set as a receiving region for receiving the signal.
In FIG. 1, the reference numerals of the transmission capacitance type cells 17a-17d and the reception capacitance type cells 18a-18d are omitted (see FIG. 2 or FIG. 3). Further, the center of the transmission cell region Rs in which the four transmission capacitance type cells 17a to 17d are arranged and the center of the reception cell region Rr in which the four reception capacitance type cells 18a to 18d are arranged are illustrated. In the radial scanning plane including the directions A and B indicated by 1, the ultrasonic waves are arranged adjacent to each other so that the directions in which the ultrasonic waves are transmitted and received are almost the same.
The rear end of the shaft 19 is connected to a rotation drive unit 21 provided in the operation unit 12. The rotation drive unit 21 incorporates a motor therein and rotationally drives the C-MUT 16 attached to the tip thereof together with the hollow shaft 19.

When the transmission ultrasonic transducer 17 constituting the C-MUT 16 performs a radial scan of the ultrasonic wave in the radial direction perpendicular to the axis of the insertion portion 11 and the reception ultrasonic transducer 18 performs a radial scan, Receive the reflected ultrasound.
The transmission ultrasonic transducer 17 includes a transmission signal cable 23 a that transmits an ultrasonic transmission signal via a transmission matching element 22 serving as a matching unit (or matching unit) provided on the transducer mounting base 20, and an end portion. Connected. In the case of the configuration shown in FIG. 2 and the like, the first matching unit or the first matching unit for the transmission signal is configured by the transmission matching element 22.
The transmission matching element 22 is configured such that the end (output end) of the transmission signal cable 23a having the first characteristic impedance value Z1 is connected to the electrical impedance of the transmission ultrasonic transducer 17 (simply simply by the transmission matching element 22). The ultrasonic transmission signal transmitted by the transmission signal cable 23a is transmitted (applied) to the transmission ultrasonic transducer 17 side in a manner matched to the impedance). In other words, the transmission matching element 22 performs impedance matching (impedance matching) on the ultrasonic transmission signal transmitted by the transmission signal cable 23a to reduce the occurrence of reflection, thereby reducing the transmission ultrasonic wave. Transmit to the vibrator 17 side.

The transmission signal cable 23a is inserted through the ultrasonic cable 13 outside the slip ring 24 via the slip ring 24 in the operation unit 12 after being inserted through the hollow portion of the shaft 19 (transmission signal). The transmission signal cable 23b (which has the same first characteristic impedance value Z1 as the cable 23a for transmission) is electrically connected. In FIG. 2, 23 a and 23 b are collectively represented by the transmission signal cable 23.
The reception ultrasonic transducer 18 is connected to a reception signal cable 26 a that transmits an ultrasonic reception signal via a reception matching element 25 as a matching means (or matching unit) provided on the transducer mounting base 20. Is done. In the case of the configuration shown in FIG. 2 and the like, the second matching unit or the second matching unit for the received signal is configured by the receiving matching element 25.
The reception matching element 25 matches the impedance of the reception ultrasonic transducer 18 that outputs the ultrasonic reception signal with the end (incident end) of the reception signal cable 26a having the second characteristic impedance value Z2. Thus, the ultrasonic reception signal output from the reception ultrasonic transducer 18 is transmitted to the reception signal cable 26a.

In other words, the reception matching element 25 performs impedance matching (impedance matching) on the ultrasonic reception signal output from the reception ultrasonic transducer 18 to reduce the occurrence of reflection, thereby reducing the reception signal. Transmit to the cable 26a side.
The reception signal cable 26a is inserted through the ultrasonic cable 13 outside the slip ring 24 via the slip ring 24 in the operation unit 12 after being inserted through the hollow portion of the shaft 19 (reception signal). (Which has the same second characteristic impedance value Z2 as that of the cable for cable 26a) and is electrically connected to the cable for received signal 26b. In FIG. 2, 26 a and 26 b are collectively shown by the reception signal cable 26.
Note that the first characteristic impedance value Z1 and the second characteristic impedance value Z2 may be the same or different.

  The transmission signal cable 23b and the reception signal cable 26b are configured to block the DC bias voltage from being applied to the transmission circuit 31 and the reception circuit 32 provided in the observation apparatus 3 via the ultrasonic connector 7. It is connected via capacitors 33 a and 33 b as elements for use, and connected to a DC bias generation circuit 35 via a switch 34. In the present embodiment, the difference in impedance value between the output end from which the transmission circuit 31 outputs the ultrasonic transmission signal and the end (input end) of the transmission signal cable 23b to which the ultrasonic transmission signal is input is set to be small. Has been. Similarly, the difference in impedance value between the end (output end) of the reception signal cable 26b and the input end of the reception circuit 32 is set to be small. A case where such conditions are not set will be described in a later-described modification.

In addition, the observation apparatus 3 includes a control circuit 36 that controls the operation of the transmission circuit 31, the reception circuit 32, and the DC bias generation circuit 35 and controls the switching operation of the switch 34.
The control circuit 36 switches and controls the switch 34 as indicated by a solid line in an ultrasonic transmission period in which ultrasonic waves are transmitted (transmitted) or an ultrasonic transmission period (hereinafter simply referred to as a transmission period).
The transmission circuit 31 generates a pulsed ultrasonic transmission signal (under the control of the control circuit 36) and superimposes the transmission signal on the DC bias voltage generated by the DC bias generation circuit 35. The signals are transmitted by the cables 23b and 23a, and applied to the four transmission capacitance type cells 17a to 17d constituting the transmission ultrasonic transducer 17 via the transmission matching element 22.

FIG. 2 shows a schematic configuration of four transmission capacitive cells 17a to 17d constituting the ultrasonic transducer 17 for transmission. The transmission capacitance type cell 17i (i = a, b, c, d) is provided with an upper electrode 37u and a lower electrode 37d so as to sandwich a gap (vacuum space region). The lower electrode 37d is conductive so as to be common to the four transmission capacitive cells 17a-17d.
In FIG. 2, four transmission capacitance type cells 17a-17d are formed in a strip-shaped region along a horizontal line, but as shown in FIG. 1, as shown in 2 rows and 2 columns. You may form in the area | region close | similar to a square. The shape of the transmission capacitive cell 17i is not limited to a square shape, but may be a circle or other shapes.

Then, an ultrasonic transmission signal superimposed on the DC bias voltage is applied to the four upper electrodes 37u via the transmission matching element 22, and each upper film vibrates to generate an ultrasonic wave, thereby transmitting capacitance. The mold cells 17a-17d send out ultrasonic waves. The transmitted ultrasonic wave is emitted from the outer peripheral surface of the distal end portion 15 toward the inner wall of the body cavity, and is reflected at a portion where the ultrasonic impedance changes.
The control circuit 36 switches and controls the switch 34 as indicated by a dotted line during an ultrasonic wave reception period (hereinafter simply referred to as a reception period) in which ultrasonic waves are received. A DC bias voltage is applied to the capacitive cells 18a to 18d, and a state of receiving ultrasonic waves is set. In addition, the control circuit 36 sets the receiving circuit 32 to an operating state.

By repeating the transmission period and the reception period (for example, from the first transmission period and the first reception period to the Nth transmission period and the Nth reception period), an ultrasonogram for generating an ultrasonic tomographic image corresponding to radial scanning is obtained. Sound wave data is acquired, and an ultrasonic tomographic image is displayed on the first monitor 4.
As shown in FIG. 2, the structure of the reception capacitance type cell 18i is the same as that of the transmission capacitance type cell 17i.
The ultrasonic wave reflected and incident from the inner wall side of the body cavity is received by the four reception capacitive cells 18a to 18d constituting the reception ultrasonic transducer 18 arranged adjacent to the transmission ultrasonic transducer 17. The received capacitive cells 18a-18d receive the ultrasonic reception signals.

The generated ultrasonic reception signal is transmitted to the reception signal cable 26 via the reception matching element 25 and is input to the reception circuit 32 from the output end of the reception signal cable 26. The receiving circuit 32 generates an ultrasonic tomographic image corresponding to mechanical radial scanning and outputs it to the first monitor 4. An ultrasonic tomographic image as an ultrasonic image is displayed on the display surface of the first monitor 4.
In addition, the ultrasonic endoscope 2 is disposed at a position near the proximal end of the distal end portion 15, a light emitting diode (abbreviated as LED) 41 as an illumination element that performs illumination, an objective lens 42, and an imaging position thereof. An image sensor 43 is provided.
The LED 41 is connected to an LED power circuit 45 in the endoscope processor 5 via a power line 44 inserted through the insertion portion 11 and the endoscope cable 14. The LED power circuit 45 supplies LED power to the LED 41 for causing the LED 41 to emit light.

The objective lens 42 connects an optical image of a subject such as an affected part illuminated by the LED 41 to the imaging surface of the imaging element 43. The image sensor 43 photoelectrically converts the optical image on the imaging surface, and outputs it to the signal processing circuit 47 in the endoscope processor 5 via the signal line 46 inserted through the insertion section 11 and the endoscope cable 14. . The signal processing circuit 47 performs signal processing for generating an endoscope image corresponding to the optical image formed on the imaging surface, outputs the endoscope image to the second monitor 6, and displays the endoscope on the display surface of the second monitor 6. An image is displayed.
In the present embodiment, as an ultrasonic probe having a C-MUT, a configuration example of an ultrasonic endoscope 2 having an endoscope function in addition to the ultrasonic probe is shown. You may make it the structure which does not have a function.

FIG. 3 shows a configuration example of the transmission matching element 22 and the reception matching element 25 in the present embodiment. The transmitting matching element 22 and the receiving matching element 25 are configured using a coil and a capacitor.
The outer conductor at the end of the coaxial cable constituting the transmission signal cable 23a is connected to the lower electrode 37d of the transmitting ultrasonic transducer 17, and the central conductor at the end of the coaxial cable is two coils 51 and 52 connected in series. Are connected to the upper electrodes 37 u of the four transmission capacitive cells 17 a to 17 d (connected in parallel) in the transmission ultrasonic transducer 17, and the connection point of the two coils 51 and 52 is connected via the capacitor 53. Connected to the (common) lower electrode 37d.
Then, the transmission ultrasonic transducer 17 is configured by using the coils 51 and 52 and the capacitor 53, and mainly the capacitance component of the four transmission capacitance type cells 17a to 17d connected in parallel and the transmission signal cable 23a. The impedance matching with the inductance component of the coaxial cable that constitutes is realized.

The lower electrode 37d of the reception ultrasonic transducer 18 is connected to the external conductor at the end of the coaxial cable constituting the reception signal cable 26a, and 4 in the transmission ultrasonic transducer 17 (connected in parallel). The two upper electrodes 37u are connected to the central conductor at the end of the coaxial cable via two coils 54 and 55 connected in series, and the connection point of the two coils 54 and 55 is connected to the lower electrode 37d via a capacitor 56. Is done.
The reception ultrasonic transducer 18 is configured using the coils 54 and 55 and the capacitor 56, and mainly includes the capacitive component of the four reception capacitive cells 18a to 18d connected in parallel, and the reception signal cable 26a. Impedance matching with the inductance component mainly of the coaxial cable constituting the.

In the present embodiment, the coil and the capacitor constituting the matching means (or matching unit) are shown in the case where they are arranged in the vicinity of the transmitting ultrasonic transducer 17 or the receiving ultrasonic transducer 18, The characteristics of the transmission capacitive cell 17a-17d constituting the transmission ultrasonic transducer 17 or the reception capacitive cell 18a-18d constituting the reception ultrasonic transducer 18, the transmission signal cable 23a or the reception You may arrange | position in the more suitable arrangement position according to the characteristic of the coaxial cable which comprises the signal cable 26a. The same applies to the case where the configuration of the matching means (or matching unit) is changed as follows.
FIG. 3 shows an example in which the transmitting matching element 22 and the receiving matching element 25 as the matching means (or matching unit) are configured using a coil and a capacitor. However, the configuration is limited to the configuration shown in FIG. It is not what is done. For example, without using a coil in FIG. 3, only a capacitor is connected in parallel to the upper electrode 37u and the lower electrode 37d in the transmitting ultrasonic transducer 17 or the receiving ultrasonic transducer 18, and is connected to both ends of this capacitor. It is also possible to connect the central conductor of the coaxial cable and the outer conductor.
Moreover, you may use the trans | transformer which converts an impedance as a matching means (or matching part).

  In the ultrasonic diagnostic apparatus 1 having such a configuration, an ultrasonic endoscope 2 as an ultrasonic probe having a capacitive ultrasonic transducer (C-MUT 16) and the ultrasonic probe are detachably connected. A transmission circuit 31 for generating an ultrasonic transmission signal for transmitting an ultrasonic wave from the capacitive ultrasonic transducer, and an ultrasonic wave generated by receiving the ultrasonic wave with the capacitive ultrasonic transducer An observation apparatus 3 as an ultrasonic observation apparatus having a reception circuit 32 that performs signal processing on a reception signal, and a plurality of transmission capacitance types that constitute the capacitive ultrasonic transducer and transmit ultrasonic waves The ultrasonic transducer 17 for transmission composed of the cells 17a-17d and a plurality of reception capacitive cells 18a-18d for receiving reflected ultrasonic waves of the transmitted ultrasonic waves and outputting ultrasonic reception signals. Receiving ultrasonic vibration A transmission signal cable 23a, 23b for connecting the transmitter 18, the transmission ultrasonic transducer 17 and the transmission circuit 31 of the ultrasonic observation apparatus, the reception ultrasonic transducer 18 and the ultrasonic observation. Transmitted by the reception signal cables 26a and 26b connecting the reception circuit 32 of the apparatus, and the ultrasonic transmission signal and the reception signal cables 26a and 26b transmitted by the transmission signal cables 23a and 23b. A transmission matching element 22 and a reception matching element 25 are provided as first and second matching units for matching electrical impedance with respect to the ultrasonic reception signal, respectively.

Next, the operation of this embodiment will be described.
As shown in FIG. 1, an ultrasonic endoscope 2 is connected to an observation device 3 and an endoscope processor 5, an insertion unit 11 is inserted into a body cavity of a patient, and an endoscopic image is observed by an image sensor 43. Below, an ultrasound examination for the affected area or the like is started.
In the first transmission period, the control circuit 36 controls the operation of the rotation drive unit 21 and also controls the operation of the transmission circuit 31, the reception circuit 32, the switch 34, and the DC bias generation circuit 35.
The transmission circuit 31 generates a pulsed ultrasonic transmission signal, superimposes the ultrasonic transmission signal on the DC bias voltage generated by the DC bias generation circuit 35, and the transmission signal cables 23 b and 23 a have the DC bias voltage. The superposed ultrasonic transmission signal is transmitted to the tip side.

The ultrasonic transmission signal superimposed on the DC bias voltage further passes through the transmission matching element 22 and is applied to the transmission capacitive cells 17a-17d constituting the transmission ultrasonic transducer 17.
In this case, impedance matching (matching) between the end portion of the transmission signal cable 23a by the transmission matching element 22 and the transmission capacitance type cells 17a-17d constituting the transmission ultrasonic transducer 17 (in parallel connection). Has been.
Therefore, the ultrasonic transmission signal is reflected by an impedance mismatch, or the reflected ultrasonic transmission signal is superimposed on the original ultrasonic transmission signal and the signal waveform is not distorted. In this state, it is applied to the four transmission capacitive cells 17a-17d (in parallel connection). For this reason, it is possible to reduce (or suppress) the occurrence of a decrease in S / N due to distortion of the signal waveform and a decrease in signal level due to reflection of the ultrasonic transmission signal.

Each of the four transmission capacitive cells 17a-17d generates an ultrasonic wave, and transmits the generated ultrasonic wave from the upper film side. By driving a plurality (four in the specific example) of the transmission capacitive cells 17a-17d, the intensity of the transmitted ultrasonic waves can be increased.
The transmitted ultrasonic wave travels to the inner wall (inner wall deep part) side of the affected part in the body cavity, is reflected at the part where the ultrasonic impedance (acoustic impedance) is changed, and is transmitted as a reflected ultrasonic cell. Return to the 17a-17d side. The control circuit 36 switches the switch 34 and applies the DC bias voltage to the reception signal cables 26b and 26a in the first reception period after the ultrasonic transmission signal is generated in the form of pulses. Then, the control circuit 36 sets the receiving circuit 32 to the operating state.

Adjacent to the transmission capacitance type cells 17a-17d, reception capacitance type cells 18a-18d constituting the reception ultrasonic transducer 18 are arranged. Therefore, the reflected ultrasonic waves that have returned are received by the reception capacitive cells 18a-18d constituting the reception ultrasonic transducer 18, converted into ultrasonic reception signals, and received capacitive cells 18a-. 18d.
The ultrasonic reception signal output from the reception capacitance type cells 18a to 18d passes through the reception matching element 25 and is input to the end of the reception signal cable 26a.
In this case, since the impedance of the reception capacitive cell 18a-18d is matched with the impedance of the end of the reception signal cable 26a by the reception matching element 25, the signal waveform is distorted due to impedance mismatch. Instead, the ultrasonic reception signal is transmitted to the reception signal cable 26a side. Therefore, it is possible to prevent a decrease in S / N and a decrease in reception sensitivity due to signal waveform distortion.

The ultrasonic reception signal transmitted to the reception signal cable 26a is input to the reception circuit 32 via the reception signal cable 26b.
The receiving circuit 32 performs image processing on the inputted ultrasonic signal and stores it as first sound ray data in the memory. When the first reception period ends, the second transmission period starts and the switch 34 is switched.
Since the C-MUT 16 is rotated by the rotation drive unit 21, the direction in which the ultrasonic waves are transmitted and received in the C-MUT 16 is slightly different from that in the first transmission period. The operation in the second transmission period is the same as that in the first transmission period except that the ultrasonic transmission direction is different.

This second transmission period is followed by a second reception period. In this case, the same operation is performed as in the case of the first reception period except that the ultrasonic wave reception direction is different. Therefore, in this case, the second sound ray data is stored in the memory.
In this way, the same operation is repeated until the Nth transmission period and the Nth reception period, and an ultrasonic tomographic image as an ultrasonic image is generated from the N sound ray data corresponding to the radial scanning, and the first monitor 4 is output. On the display surface of the first monitor 4, an ultrasonic tomographic image is generated that has less reflection of an ultrasonic transmission signal and an ultrasonic reception signal and distortion of the signal waveform, and therefore has high reception sensitivity and good S / N. Is done.
As described above, the present embodiment includes matching means (or a matching unit) for matching the electrical impedance with respect to the ultrasonic transmission signal at the time of ultrasonic transmission and the ultrasonic reception signal at the time of ultrasonic reception. ing. Further, in order to perform transmission and reception of ultrasonic waves, dedicated ultrasonic transducers 17 and ultrasonic transducers 18 for reception are provided.

Therefore, according to the present embodiment, it is possible to prevent a decrease in reception sensitivity due to any impedance mismatch during transmission of ultrasonic waves and reception of ultrasonic waves, and ultrasonic waves with good reception sensitivity and S / N. Images can be acquired. More specifically, according to the present embodiment, it is possible to reduce distortion of the signal waveform due to reflection of the ultrasonic transmission signal due to impedance mismatch, to prevent a reduction in the intensity of the ultrasonic wave due to reflection, and to receive ultrasonic waves When the ultrasonic wave reception signal generated by receiving by the transducer 18 is transmitted to the reception circuit 32 side via the reception signal cables 26a and 26b, the distortion of the signal waveform due to reflection due to impedance mismatching is reduced and the signal intensity is reduced. Can be prevented, and an ultrasonic image with good S / N can be acquired. Moreover, according to this embodiment, since an ultrasonic image with a good S / N can be acquired, an operator who makes a diagnosis from observation of an ultrasonic image can easily perform an appropriate diagnosis.
In addition, since the ultrasonic transducer for transmission 17 and the ultrasonic transducer for reception 18 that are dedicated at the time of transmission of ultrasonic waves and at the time of reception of ultrasonic waves are used, it is more appropriate than when both transmission and reception are used. With such characteristics, it is possible to transmit ultrasonic waves and receive ultrasonic waves, and to perform impedance matching more appropriately in that case. Therefore, according to this embodiment, it is possible to perform transmission of ultrasonic waves and reception of ultrasonic waves in a state that is ideally closer than in the conventional example.

FIG. 4 shows a configuration of a circuit system that transmits and receives ultrasonic waves according to a modification of the present embodiment. In the first embodiment described above, the difference between the impedance value of the output terminal of the transmission circuit 31 and the impedance value of the input terminal of the transmission signal cable 23b is small, and the impedance value of the output terminal of the reception signal cable 26b is small. And the difference between the impedance value of the input terminal of the receiving circuit 32 is small.
If the difference between these impedance values is not small, a second transmission signal matching element 61 is provided between the output end of the transmission circuit 31 and the input end of the transmission signal cable 23b as shown in FIG. Further, the second reception signal matching element 62 may be arranged between the output end of the reception signal signal cable 26 b and the input end of the reception circuit 32. In this case, the second transmission signal matching element 61 and the second reception signal matching element 62 may be provided, for example, inside the ultrasonic connector 7 shown in FIG. In the case of the configuration shown in FIG. 4, the first matching unit or the first matching unit for the transmission signal is configured by the transmission signal matching element 22 and the second transmission signal matching element 61, and the second matching for the reception signal. The matching means or the second matching unit is constituted by a received signal matching element 25 and a second received signal matching element 62.
In FIG. 4, the plurality of transmission capacitive cells 17a-17d and the plurality of reception capacitance cells 18a-18d shown in FIG. A simplified ultrasonic transducer 18 is shown. In FIG. 4, the control circuit 36 is omitted.

The second transmission signal matching element 61 and the second reception signal matching element 62 are configured using the transmission matching element 22 and the reception matching element 25 using coils and capacitors as shown in FIG. Alternatively, a capacitor may be used, or another known element may be used.
As shown in FIG. 4, by providing a second transmission signal matching element 61 and a second reception signal matching element 62, an ultrasonic transmission signal is transmitted (output) from the transmission circuit 31 to the transmission signal cable 23 side. ) Signal waveform distortion (due to impedance mismatch) when the ultrasonic reception signal is input from the reception signal cable 26 to the reception circuit 32 (due to impedance mismatch), etc. Can be reduced.
Therefore, in addition to the effects of the first embodiment described above, it is possible to obtain an ultrasonic image with better reception sensitivity and S / N.

(Second Embodiment)
FIG. 5 shows a schematic configuration of an ultrasonic diagnostic apparatus 1B according to the second embodiment of the present invention. This ultrasonic diagnostic apparatus 1B includes an ultrasonic probe 71, an observation apparatus 3, and a first monitor 4.
Although the ultrasonic endoscope 2 is provided in FIG. 1, in this embodiment, an ultrasonic probe 71 is used instead. The ultrasonic probe 71 has a structure that does not have an endoscope function (the LED 41, the objective lens 42, and the imaging device 43) in the ultrasonic endoscope 2 of FIG. In FIG. 5, the rotation drive unit 21 and the like are omitted.

In the first embodiment described above, the four transmission capacitance cells 17a to 17d in the transmission cell region Rs perform impedance matching in common by one transmission matching element 22, and the reception cell region. The four reception capacitive cells 18a to 18d in Rr are configured to perform impedance matching in common by one reception matching element 25.
On the other hand, in the present embodiment, impedance matching is performed by the transmission matching element 22i for each transmission capacitance cell 17i in the transmission cell region Rs (that is, for each transmission capacitance cell 17i). Thus, impedance matching is performed by the receiving matching element 25i for each receiving capacitive cell 18i in the receiving cell region Rr.

For example, the transmission capacitance type cell 17a (the upper electrode 37u and the lower electrode 37d thereof) in the transmission cell region Rs has an impedance formed by the transmission matching element 22a arranged in the vicinity of the transmission capacitance type cell 17a or in the vicinity thereof. Matching is performed, and the central conductor and the outer conductor at the end of the coaxial cable constituting the transmission signal cable 23a are connected. The same applies to the other transmission capacitance type cells 17b-17d.
Further, for example, the reception capacitive cell 18a (the upper electrode 37u and the lower electrode 37d thereof) in the reception cell region Rr is impedance-matched by the reception matching element 25a disposed in the vicinity of the reception capacitance cell 18a. And the center conductor and the outer conductor at the end of the coaxial cable constituting the reception signal cable 26a are connected. The same applies to the other receiving capacitance type cells 18b-18d.

The transmission matching element 22i and the reception matching element 25i may be configured using, for example, a coil and a capacitor shown in FIG. 3, may be configured using a capacitor, or other known elements. You may comprise using.
The configuration of the observation device 3 has been described with reference to FIG.

  According to the present embodiment, even when there are variations in characteristics (for example, impedance values) among a plurality (four in the specific example) of transmission capacitance cells 17a-17d in the transmission cell region Rs. The transmission matching element 22i can perform impedance matching with the transmission signal cable 23a in accordance with the characteristics of the individual transmission capacitance type cells 17i.

Further, according to the present embodiment, the characteristics (for example, impedance values) of the plurality of (four in the specific example) reception capacitance type cells 18a to 18d in the reception cell region Rr vary. The impedance matching with the reception signal cable 26a can be performed by the reception matching element 25i according to the characteristics of the individual reception capacitance type cell 18i.
Therefore, it has the same effect as the first embodiment, and further has the effect of further improving the reception sensitivity and S / N. Also in this embodiment, the second transmission matching element 61 and the second reception matching element 62 shown in FIG. 4 may be provided.

(Third embodiment)
FIG. 6 shows a schematic configuration of an ultrasonic diagnostic apparatus 1C according to the third embodiment of the present invention. This ultrasonic diagnostic apparatus 1 </ b> C includes an ultrasonic probe 71 </ b> C, an observation apparatus 3, and a first monitor 4.
In the ultrasonic diagnostic apparatus 1B shown in FIG. 5, the transmission cell region Rs and the reception cell region Rr are formed adjacent to each other, but in the present embodiment, the ultrasonic probe 71 shown in FIG. The transmission capacitance type cells 17a and 17c and the reception capacitance type cells 18b and 18d are mixed in the transmission / reception cell region Rs / Rr having the same size as the transmission cell region Rs or the reception cell region Rr. The ultrasonic probe 71C is formed by arranging.

The transmission capacitance type cells 17a and 17c perform impedance matching with the transmission signal cable 23a by the transmission matching elements 22a and 22c, respectively, and the reception capacitance type cells 18b and 18d respectively receive the matching elements for reception. The impedance matching with the reception signal cable 26a is performed by 25b and 25d.
Other configurations are the same as those shown in FIG.
According to the present embodiment, a transmission area for transmitting ultrasonic waves for generating information for one pixel in an ultrasonic image and a reception area for receiving ultrasonic waves for acquiring information for one pixel are common. Therefore, an ultrasonic image with high resolution can be acquired.

Similarly to the case of the second embodiment, impedance values are set between the transmission capacitive cells 17a and 17c and between the reception capacitive cells 18b and 18d in the transmission / reception cell region Rs / Rr. Even when there is a variation, impedance matching can be performed according to the characteristics of the individual transmission capacitive cells 17a and 17c and the reception capacitive cells 18b and 18d. For this reason, an ultrasonic image with good reception sensitivity and S / N can be acquired.
Also in this embodiment, the second transmission matching element 61 and the second reception matching element 62 shown in FIG. 4 may be provided.
In the above-described embodiment, the ultrasonic diagnostic apparatus that mechanically scans the C-MUT 16 has been described. However, the present invention can also be applied to an ultrasonic diagnostic apparatus that electrically scans the C-MUT.

FIG. 7 shows a configuration of an ultrasonic diagnostic apparatus 1D of the second modification example of the first embodiment that electronically scans instead of the ultrasonic diagnostic apparatus 1 that mechanically scans the C-MUT 16 of FIG. 1, for example. . This ultrasonic diagnostic apparatus 1D includes an endoscope 2D instead of the endoscope 2 in the ultrasonic diagnostic apparatus 1 of FIG. The endoscope 2D is provided with a transmitting ultrasonic transducer 17 and a receiving ultrasonic transducer 18 that constitute the C-MUT 16 adjacent to each other along the outer peripheral surface of the distal end portion 15. Further, the ultrasonic transducer for transmission 17 and the ultrasonic transducer for reception 18 respectively include n transmission capacitance type cells 17a-17n and reception capacitance type cells 18a-18n along a (circular) line. It is constituted by an arranged ultrasonic transducer array. It should be noted that the transmitting cell region and the receiving cell region corresponding to the entire ultrasonic scanning region are the annular regions where the transmitting capacitive cells 17a-17n and the receiving capacitive cells 18a-18n are respectively arranged. Form. In the present modification, the transmitting cell region Rs1 and the receiving cell region Rr1 move (change) according to the scanning direction of the ultrasonic wave that changes with time, as will be described later. For this reason, the transmission capacitance type cell 17k and the reception capacitance type cell 18k also move in accordance with the movement of the transmission cell region Rs1 and the reception trusted cell region Rr1.
In addition, the transmission capacitance type cell 17j (j = a, b, c,..., N) is connected to, for example, n terminals of the first multiplexer 81A arranged in the distal end portion 15, and is connected to the control circuit 36. A decoder 84A to which a clock (mode signal) as a selection control signal (synchronized with the transmission period described above) transmitted by the cable 80 is applied is provided in the vicinity of the first multiplexer 81A. The decoder 84A generates a selection signal from an applied (input) clock, and outputs the generated selection signal to the first multiplexer 81A. The first multiplexer 81A can select a plurality of n (for example, 3) by the selection signal. Sequentially). A DC bias voltage is superimposed by the transmission signal cable 23 on the three selected transmission capacitance type cells 17k (k = a, b, c; b, c, d; c, d, e;...). In this state, an ultrasonic transmission signal from the transmission circuit 31 is applied. As described above, when the selection control signal is input, the decoder 84A selects a plurality (three in the specific example) of transmission capacitance type cells 17k used for ultrasonic transmission to the first multiplexer 81A. A selection signal is generated.
The transmission signal cable 23 transmits the ultrasonic transmission signal and the DC bias voltage from the observation device 3 to which the ultrasonic connector 7 is connected, and the first multiplexer 81A in the distal end portion 15 and the transmission ultrasonic transducer. The signal is applied to the three transmission capacitive cells 17k selected by the first multiplexer 81A through the transmission matching element 82 constituting the matching means (or matching unit) arranged in the vicinity of the first multiplexer 81A.

  The first multiplexer 81A transmits the transmission capacitive cells 17a, 17b, and 17c according to the selection signal from the decoder 84A during the H level period of the first clock synchronized with the first transmission period in the selection control signal. The transmission capacitive cells 17b, 17c, and 17d are selected during the H level period of the second clock, and the transmission capacitive cells 17c, 17d are selected during the H clock period of the third clock. Three transmission capacitance type cells 17k are sequentially selected according to the order of arrangement such as selecting 17d and 17e. FIG. 8 is a timing chart for explaining the operation of the clock as the selection control signal applied (input) to the decoder 84A and the selection signal output from the decoder 84A. The first, second,... Clocks (abbreviated as first CLK, second CLK,...) As selection control signals are output in synchronization with the first, second,... Transmission periods (Ts1, Ts2,...). . The decoder 84A generates three cell selection signals 85a, 85b, and 85c as selection signals from such a clock and outputs them to the three selection control terminals that control the selection of the first multiplexer 81A. Note that the decoder 84A (the same applies to a decoder 84B described later) is configured using a ring counter that counts clocks, an adder circuit that adds clocks, and the like (not shown). In FIG. 8, a clock as a selection control signal whose H level and L level periods are synchronized with the transmission period and the reception period, respectively, is generated from a reference clock (not shown).

When the first clock as the selection control signal synchronized with the first transmission period Ts1 as the first transmission period is input to the decoder 84A, the decoder 84A counts the rising edges and outputs an output value (total) from the first output terminal. As the numerical value, only the 1-bit digit outputs the H-level cell selection signal 85a, and the output value from the second output end (1 bit added to 1 bit from the first output end), 2 bits, H level Cell selection signal 85b is output, and a 3-bit, H-level cell selection signal 85c is added from the third output terminal as an output value (1 bit added to 2 bits from the second output terminal). Output to the selection control terminal. The first multiplexer 81A is set to select three transmission capacitive cells 17k according to the number of bits as the output value of the cell selection signals 85a, 85b, 85c output from the decoder 84A. For example, when the number of bits Ba of the cell selection signal 85a (the same applies to 85b and 85c) is Ba = 1 bit, the transmission capacitance type cell 17a, and when Ba = 2 bits, the transmission capacitance type cell 17b, ..., Ba = n bits, the transmission capacitance type cell 17n is set to be selected. Note that n represents the number of transmission capacitive cells as described above.
When the bit number Ba becomes Ba = n, the decoder 84A resets the bit number Ba to 0 immediately before the next (n + 1) th clock is input, and once again when the (n + 1) th clock is input. The bit cell selection signal 85a is set to be output. Therefore, when the bit numbers of the cell selection signals 85a, 85b, and 85c are 1, 2, and 3 bits, respectively, the first multiplexer 81A transmits the transmission capacitance in the first, second, and third arrangement order. The type cells 17a, 17b, and 17c are selected.

  When a second clock is input as a selection control signal synchronized with the second transmission period Ts2, 2 bits are output from the first output terminal (adding 1 bit to the previous 1 bit) as H The cell selection signal 85a of the level is output, the cell selection signal 85b of 3 bits and H level is output as the output value from the second output terminal (1 bit is added to 2 bits from the first output terminal), A 4-bit, H-level cell selection signal 85c is output from the output terminal 3 to the first multiplexer 81A as an output value (1 bit added to 3 bits from the second output terminal). Accordingly, in this case, the first multiplexer 81A selects the transmission capacitive cells 17b, 17c, and 17d that are in the second, third, and fourth arrangement order. In accordance with the order arranged in such a manner, the three transmission capacitive cells 17k are sequentially selected. Then, the selected three transmission capacitive cells 17k transmit ultrasonic waves radially, and perform radial scanning of the ultrasonic waves (beams). In the present modification, a transmission cell region Rs1 for generating an ultrasonic beam for one pixel is formed by three transmission capacitance type cells 17k, and the transmission cell region Rs1 performs a radial scan of ultrasonic waves. The transmission ultrasonic transducer 17 (that is, the n transmission capacitive cells 17a to 17n) that forms the transmission region of the case moves in accordance with the direction (or radial narrow region) in which ultrasonic waves are transmitted. However, a predetermined transmission cell region Rs1 is determined according to the direction (or radial narrow region) in which the ultrasonic waves are transmitted. On the other hand, in the first embodiment, the transmission cell region Rs is common even if the direction in which ultrasonic waves are transmitted changes.

  The transmission matching element 82 includes, for example, three parallel-connected transmissions that are used for ultrasonic transmission by the transmission matching element 82 at the end (output end) of the transmission signal cable 23 having the first characteristic impedance value Z1. The ultrasonic transmission signal transmitted through the transmission signal cable 23 is matched (matched) with the impedance of the capacitance type cell 17k and transmitted (applied) to the transmission capacitance type cell 17k. In other words, the transmission matching element 82 performs impedance matching (impedance matching) on the ultrasonic transmission signal transmitted by the transmission signal cable 23 to reduce the occurrence of reflection, thereby transmitting ultrasonic waves. The voltage is applied to the three transmission capacitive cells 17k constituting the vibrator 17. In the illustrated example of FIG. 7, matching is made to the impedance of three parallel-connected transmission capacitance type cells 17k selected by one transmission matching element 82, but one selected transmission capacitance type is selected. Impedance matching may be performed for each cell 17k. Further, when impedance matching is performed for each transmission capacitance type cell 17k, the transmission signal cable 23 may be constituted by three coaxial cables as shown in FIG.

  As shown in FIG. 9, the end portions of the three coaxial cables 23-1, 23-2, and 23-3 constituting the transmission signal cable 23 are respectively aligned with one transmission capacitance type cell 17k. Are connected to the respective transmission capacitance type cells 17k selected by the first multiplexer 81A through the transmission matching elements 82-1, 82-2 and 82-3. In the case of three coaxial cables 23-1, 23-2, and 23-3, the three transmission circuits 31-1 and 31 that constitute the transmission circuit 31 are arranged on the proximal end as indicated by a two-dot chain line. It may be configured to connect to −2, 31-3, respectively. The capacitor 33a is not shown.

Similarly, the reception capacitance type cell 18j (j = a, b, c,..., N) is connected to, for example, n terminals of the second multiplexer 81B disposed in the distal end portion 15, and is connected to the control circuit 36. A decoder 84B to which a selection control signal transmitted by the cable 80 is applied is provided in the vicinity of the second multiplexer 81B. The decoder 84B generates a selection signal from the selection control signal to be applied (input), and outputs the generated selection signal to the second multiplexer 81B. For example, select 3). The selected three reception capacitance type cells 18k receive the ultrasonic waves in the case of radial scanning, and generate ultrasonic reception signals. As described above, when the selection control signal is input, the decoder 84A selects a plurality (three in the specific example) of received capacitive cells 18k to be used for reception of ultrasonic waves with respect to the second multiplexer 81B. Generate a signal.
The ultrasonic reception signals generated by the three reception capacitive cells 18k constitute a matching means (or matching unit), and are received via a reception matching element 83 arranged in the vicinity of the reception ultrasonic transducer 18. The ultrasonic reception signal is transmitted to the reception circuit 32 in a state where the DC bias voltage is superimposed by the signal cable 26.

As described above, the reception signal cable 26 transmits the ultrasonic reception signal generated by the three transmission capacitive cells 17k selected by the second multiplexer 81B through the reception matching element 83 and the reception signal cable 26. The ultrasonic reception signal is transmitted to the reception circuit 32 in the observation apparatus 3.
Similar to the case of the first multiplexer 81A, the second multiplexer 81B receives the selection signal from the decoder 84B during the L level period of the first clock synchronized with the first reception period in the selection control signal. The reception capacitance type cells 18a, 18b, and 18c are selected, and the reception capacitance type cells 18b, 18c, and 18d are selected in the period of the L level of the second clock, and the L level of the third clock is further selected. In the period, the receiving capacitive cells 18c, 18d, 18e are selected, and the three receiving capacitive cells 18k are sequentially selected according to the arrangement order of the receiving capacitive cells 18j. FIG. 8 also shows the timing for explaining the operation of the selection control signal applied (input) to the decoder 84B and the selection signal output from the decoder 84B. The operation in this case is similar to the description related to the decoder 84A in the transmission period described above as follows.

As shown in the figure, the L level of the first, second,... Clock is output as a selection control signal in synchronization with the first, second,... Reception periods Tr1, Tr2,. The decoder 84B generates three cell selection signals 86a, 86b, 86c constituting the selection signal from such falling edges of the clock, and outputs them to the selection control terminal of the second multiplexer 81B.
When the first clock is input as the selection control signal synchronized with the first reception period Tr1 that is the first reception period, the decoder 84B outputs only 1 bit as an output value (count value) from the first output terminal. A cell selection signal 86a of level is output, and a 2-bit, H-level cell selection signal 86b is output as an output value from the second output terminal (1 bit added to 1 bit from the first output terminal) The 3-bit, H-level cell selection signal 86c is output from the output terminal 3 to the selection control terminal of the second multiplexer 81B as an output value (1 bit added to 2 bits from the second output terminal). The second multiplexer 81B is set to select three reception capacitive cells 18k in accordance with the number of bits as the output value of the cell selection signals 86a, 86b, 86c output from the decoder 84B. For example, when the bit number Bb of the cell selection signal 86a (86b, 86c is the same) is Bb = 1 bit, the received capacitive cell 18a, and when Bb = 2 bit, the received capacitive cell 18b, ..., Bb = n bit, the receiving capacitance type cell 18n is set to be selected. Note that n represents the number of received capacitive cells as described above.
Further, the decoder 84B resets the bit number Bb to 0 immediately before the next (n + 1) th clock is inputted when the bit number Bb becomes Bb = n, and once again when the (n + 1) th clock is inputted. The bit cell selection signal 86b is set to be output. Therefore, when the cell selection signals 8ba, 8bb, and 8bc have 1, 2, and 3 bits, respectively, the second multiplexer 81B receives the first, second, and third arrangement order of receiving capacitances. Cells 18a, 18b, 18c are selected.

When the second clock is input as the selection control signal synchronized with the second reception period Tr2, the output value is output from the first output terminal (adding 1 bit to the previous 1 bit), 2 bits, H level Cell selection signal 86a is output from the second output terminal, and a 3-bit, H-level cell selection signal 86b is output as an output value (one bit is added to the two bits from the first output terminal). The 4-bit, H-level cell selection signal 86c is output to the second multiplexer 81B as an output value (1 bit added to 3 bits from the second output end). Therefore, in this case, the second multiplexer 81B selects the reception capacitive cells 18b, 18c, and 18d in the second, third, and fourth arrangement order. The three receiving capacitive cells 18k are sequentially selected according to the order arranged in such a manner.
Then, ultrasonic waves are received when the selected three reception capacitive cells 18k are scanned radially. In the present modification, a reception cell region Rr1 for generating an ultrasonic reception signal for one pixel is formed by three reception capacitance type cells 18k, and as in the case of the transmission cell region Rs1, In accordance with the direction (or radial narrow area) in which the ultrasonic waves are received in the reception ultrasonic transducer 18 (that is, the n reception capacitive cells 18a to 18n) that forms the reception area of the ultrasonic waves for radial scanning. Move. However, a predetermined reception cell region Rr1 is determined according to the direction in which the ultrasonic waves are received (or a narrow radial region). On the other hand, in the first embodiment, the reception cell region Rr is common even if the direction in which the ultrasonic wave is received changes.

The reception matching element 83 causes the impedances of the three reception capacitive cells 18k that output ultrasonic reception signals to be at the end (incident end) of the reception signal cable 26 having the second characteristic impedance value Z2. The ultrasonic reception signals output from the three reception capacitive cells 18k are transmitted through the reception signal cable 26 by matching.
In other words, the reception matching element 83 performs impedance matching (impedance matching) on the ultrasonic reception signals output from the three reception capacitive cells 18k to reduce the occurrence of reflection. The signal is transmitted to the reception signal cable 26 side. In the illustrated example of FIG. 7, the impedances of the selected three reception-connected capacitive cells 18 k connected in parallel are matched with the reception signal cable 26 by one reception matching element 83. Impedance matching may be performed for each of the two reception capacitance type cells 18k. When impedance matching is performed for each reception capacitance type cell 18k, the reception signal cable 26 may be configured by three coaxial cables as shown in FIG.
As shown in FIG. 9, the end portions of the three coaxial cables 26-1, 26-2, 26-3 constituting the reception signal cable 26 are received matching elements 83-1, 83-2, 83, respectively. -3 to the respective reception capacitive cells 18k selected by the second multiplexer 81B. In the case of three coaxial cables 26-1, 26-2, 26-3, as shown by a two-dot chain line, three receiving circuits 32-1, You may make it the structure connected to 32-2, 32-3, respectively. The illustration of the capacitor 33b is omitted.

  7 and 9, as the transmission cell region Rs1 and the reception cell region Rr1, the transmission capacitive cell 17k (k = a, b, c) initially selected by the selection signal and the reception cell region Rs1 are received. A capacitive cell 18k is shown. As described above, the transmission cell region Rs1 and the reception cell region Rr1 for generating one pixel are sequentially moved by the selection signal. The same operation is repeated with the acquisition of an ultrasonic image for one frame as a cycle. Other configurations are the same as those of the first embodiment described above, and the description thereof is omitted.

    Note that an ultrasonic tomographic image for one pixel is generated from the ultrasonic reception signal in the j-th transmission reception period Tj including the j-th transmission period Tsj and the j-th reception period Trj. Here, j = 1, 2,... N.

  This modification is basically the same operation except that the operation in which the first embodiment mechanically scans ultrasonic waves is changed to an operation in which ultrasonic waves are electronically scanned. Also in the present modification, in the first transmission period Ts1, the ultrasonic transmission signal superimposed on the DC bias voltage from the transmission circuit 31 is transmitted through the transmission signal cable 23 to the three transmission capacitive cells 17a, 17b, When transmitting to 17c, it passes through the transmission matching element 82 provided at the end of the transmission signal cable 23, and is applied to the transmission capacitive cells 17a, 17b, 17c constituting the transmission ultrasonic transducer 17. .

In this case, as shown in FIG. 7, the transmission matching element 82 constitutes the end of the transmission signal cable 23 and the transmission ultrasonic transducer 17 (in parallel connection), three transmission capacitance type cells 17a, Impedance matching (matching) with 17b and 17c is performed. In FIG. 9, impedance matching is performed for each of the transmission capacitive cells 17a, 17b, and 17c.
Therefore, the ultrasonic transmission signal is reflected by an impedance mismatch, or the reflected ultrasonic transmission signal is superimposed on the original ultrasonic transmission signal and the signal waveform is not distorted. In this state, it is applied to the three transmission capacitance type cells 17a, 17b and 17c (in parallel connection). For this reason, it is possible to reduce (or suppress) the occurrence of a decrease in S / N due to distortion of the signal waveform and a decrease in signal level due to reflection of the ultrasonic transmission signal.

In the first reception period Tr1 following the first transmission period Ts1, the ultrasonic reception signals output from the reception capacitive cells 18a, 18b, and 18c pass through the reception matching element 83 and are used for reception signals. Input to the end of the cable 26.
In this case, since the impedance of the reception capacitive cells 18a, 18b, 18c and the impedance of the end of the reception signal cable 26 are impedance matched by the reception matching element 83, the signal waveform is caused by impedance mismatch. The ultrasonic reception signal is transmitted to the reception signal cable 26 side without being distorted. Therefore, it is possible to prevent a decrease in S / N and a decrease in reception sensitivity due to signal waveform distortion.
The ultrasonic reception signal transmitted to the reception signal cable 26 is input to the reception circuit 32 via the reception signal cable 26.

The receiving circuit 32 performs image processing on the inputted ultrasonic signal and stores it as first sound ray data in the memory. When the first reception period Tr1 ends, the second transmission period Ts2 is reached and the switch 34 is also switched. And the direction which transmits / receives an ultrasonic wave turns into a slightly different direction from the case of 1st transmission period Ts1. The operation in the second transmission period Ts2 is the same as that in the first transmission period Ts1, except that the ultrasonic transmission direction is different. The operation in the second reception period Tr2 is the same as that in the first reception period Tr1 except that the ultrasonic wave reception direction is slightly different.
Therefore, the ultrasonic diagnostic apparatus 1D of FIG. 7 has substantially the same effect as that of the first embodiment shown in FIG. In the above description, a case where three are selected as an example of selecting a plurality of transmission capacitive cells 17k and a plurality of reception capacitance cells 18k has been described. However, a single or a plurality other than three is selected. May be selected. Further, although the case of radial scanning has been described, the present invention is not limited to the case of radial scanning, and other scanning, for example, convex scanning, may be performed.
Moreover, although this modification demonstrated in FIGS. 7-9 demonstrated the case where it applied to the electronic scanning in 1st Embodiment of FIG. 1, it can also be applied to other embodiment etc.
In the case of the mechanical scanning of the first embodiment, the following may be performed. In the case of the mechanical scanning of the first embodiment, the transmission period Tsj for one pixel by the four transmission capacitance type cells 17a-17d and the four reception capacitance type cells are used as the motor in the rotation drive unit 21. A stepping motor 21a (indicated by a dotted line in FIG. 1) that rotates stepwise every time a reception period Trj for one pixel by 18a-18d elapses may be used. FIG. 10 shows the change timing of the ultrasonic transmission / reception period Tj for one pixel, which is composed of the transmission period Tsj for one pixel and the reception period Trj, and the rotation angle θj of the stepping motor 21a in this case. The ultrasonic transmission / reception period Tj for one pixel corresponds to a period for generating one pixel in a period for generating an ultrasonic tomographic image for one frame.

  As shown in FIG. 10, in the ultrasonic transmission / reception period Tj for the same one pixel, the rotation angle θj of the stepping motor 21a does not change, so that it exceeds one pixel by the four transmission capacitive cells 17a-17d. The reflected signal of the sound wave can be efficiently received by the four reception capacitive cells 18a to 18d arranged so as to be adjacent to each other. That is, there is an effect of increasing the S / N when receiving. In FIG. 10, the transmission capacitance type cell and the reception capacitance type cell are abbreviated as a transmission cell and a reception cell, respectively. The transmission capacitance type cells 17a-17d and the reception capacitance type cells 18a-18d operate in the transmission period Tsj and the reception period Trj indicated by the H level, respectively.

  The DC bias voltage generated by the DC bias generation circuit 35 is alternately switched between the transmission period Tsj and the reception period Trj. In FIG. 10, a period during which the DC bias voltage is applied to the transmission capacitance type cells 17a-17d is indicated by symbol a, and a period during which the DC bias voltage is applied to the reception capacitance type cells 18a-18d is indicated by symbol b. Further, for example, the variable capacitors 53a and 56a constituted by trimmer capacitors or the like whose capacitance can be varied as indicated by dotted lines in the capacitors 53 and 54 shown in FIG. The impedance may be adjusted. In other words, the first matching unit that performs matching with respect to the transmission signal includes a first element having a predetermined impedance value and a second element that can vary the impedance value, or performs matching with respect to the reception signal. The second matching unit may include a third element having a predetermined impedance value and a fourth element that can vary the impedance value.

  With such a configuration, even when the impedances of the transmission capacitive cells 17a-17d and the reception capacitive cells 18a-18d change over time, the impedances of the transmission matching element 22 and the reception matching element 25 are reduced. By adjusting the capacitance of the trimmer capacitor, adjustment can be easily performed so that impedance matching can be maintained.

  When the impedances of the transmission capacitance type cells 17a-17d and the reception capacitance type cells 18a-18d change over time, a transmission signal is transmitted from the transmission signal cable 23a to the transmission capacitance type cells 17a-17d or received. When a reception signal is transmitted from the capacitance type cells 18a to 18d to the reception signal cable 26a, mismatching occurs. However, it becomes easy to match by changing the capacitance of the trimmer capacitor.

  Further, for example, even when there is an individual difference in impedance (capacitance) between the transmission capacitive cells 17a-17d and the reception capacitive cells 18a-18d used in the product, a common transmission matching element 22 and the receiving matching element 25 can be used to absorb differences between products by adjusting the trimmer capacitor. In addition, you may apply the element which varies the electrostatic capacitance using the trimmer capacitor shown in FIG. 3 to embodiment other than FIG. For example, the transmission matching element 22 having a trimmer capacitor can be applied to FIG. 4, the transmission matching elements 22 a to 22 d in FIG. 5, the transmission matching elements 22 a and 22 c in FIG. 6, and the transmission matching element in FIG. 7. The present invention can be applied to the matching element 82, the transmission matching elements 82-1 to 82-3 in FIG. 9, and can also be applied to the second transmission matching element 61 in FIG.

  Further, for example, the receiving matching element 25 having a trimmer capacitor can be applied to FIG. 4, and the receiving matching elements 25a to 25d in FIG. 5, the receiving matching elements 25b and 25d in FIG. The present invention can be applied to the receiving matching element 83, the receiving matching elements 83-1 to 83-3 in FIG. 9, and can also be applied to the second receiving matching element 62 in FIG.

  Further, for example, with respect to the transmission ultrasonic transducer 17 and the reception ultrasonic transducer 18 shown in FIG. 4, a transmission signal cable 23a and a reception signal cable 26a are respectively provided by a transmission matching element 22 and a reception matching element 25. The reference waveform (reference waveform) in which ultrasonic waves are transmitted to and received from the reference ultrasonic object in advance and the capacitance value of the trimmer capacitor in the matched state are not changed. In a matched state, a threshold waveform that is an allowable boundary from the reference waveform may be examined in advance and stored in a storage unit such as a nonvolatile memory. When the ultrasonic endoscope 2 is used for an appropriate period, the ultrasonic wave is transmitted and received using the reference ultrasonic object, and whether or not the waveform is within the allowable range is stored in the storage unit. By comparing with a stored reference waveform or threshold waveform, it may be possible to determine whether the matching state is maintained or whether it deviates from the range of the control state that is allowed due to secular change or the like.

  As the reference ultrasonic object, for example, ultrasonic waves are reflected only at a certain distance (one or more) from the transmission capacitive cells 17a-17d and the reception capacitive cells 18a-18d. Prepare an object that does not reflect at other distances. In the mismatched state, the signal level from a certain distance position decreases and the signal level at other distances increases due to mismatching. It can be determined whether or not it is maintained.

  For this reason, in the observation apparatus 3 of FIG. 1, the reference waveform and the threshold waveform measured in the aligned state with respect to the reference ultrasonic object using the ultrasonic endoscope 2 or the representative waveform in the reference waveform and the threshold waveform. A storage unit 40 (indicated by a dotted line) for storing the signal level at a specific distance in association with the ultrasonic endoscope 2 used for the measurement may be provided.

  When the measurement waveform measured on the reference ultrasonic object is displayed on the first monitor 4, the control circuit 36 compares the reference waveform or the like stored in the storage unit 40 with the measurement waveform on the first monitor 4. To make it easier to do. The display color is controlled to be superimposed and displayed.

  The user can easily identify whether or not the alignment state is maintained from the measurement waveform displayed on the first monitor 4 and the reference waveform. In addition, the control circuit 36 compares the measurement waveform with the reference waveform, etc., and determines whether the range is within the allowable matching state within the threshold waveform or is in an inconsistent state deviating from the threshold waveform (indicated by a dotted line) ) You may make it have the function of the determination part 36a.

  In other words, the following configuration may be added. The reference waveform of the ultrasonic wave reception signal obtained by setting the first and second matching portions to the matching state with respect to the reference reference ultrasonic object and the mismatch from the reference waveform to an allowable boundary When storing ultrasonic waves to and from the reference ultrasonic object, the storage unit 40 stores in advance information on the reference and threshold signal level at least at a representative distance in the threshold waveform acquired when Determination of whether or not the first and second matching units are in a matching state from a comparison between the signal level of the obtained ultrasonic reception signal and the reference and threshold signal levels read from the storage unit The portion 36a may be provided. Note that the determination unit 36 a may be formed by a comparison circuit or the like provided outside the control circuit 36.

  Only one of the reference waveform and the threshold waveform may be stored in the storage unit 40.

  Further, instead of providing the storage unit 40 in the observation apparatus 3, an identification information storage unit for storing identification information unique to the ultrasonic endoscope 2 is provided in the connector 7 of the ultrasonic endoscope 2 in FIG. The information stored in the storage unit 40 may be stored in the identification information storage unit. For example, the control circuit 36 may control the same as in the case of the storage unit 40. 1 is provided with the storage unit 40 and the like, it may be provided in FIGS. 2, 4, 5, 6, and 7. FIG.

  In addition, embodiments configured by partially combining the above-described embodiments and the like also belong to the present invention. For example, an embodiment in which the arrangement position of the matching portion is changed also belongs to the present invention.

  Further, the present invention is not limited to all the components disclosed in the present specification, but the components described in claim 1 disclosed in the present invention are reduced to the minimum necessary for the present invention. It may be a limited component. Further, a configuration in which one or a plurality of components are appropriately or selectively added to the minimum components in the specification or claims other than claim 1 may be adopted.

  This application is filed on the basis of the priority claim of Japanese Patent Application No. 2012-019998 filed in Japan on February 1, 2012, and the above disclosure is included in the present specification and claims. Shall be quoted.

An ultrasonic diagnostic apparatus according to one embodiment of the present invention includes an ultrasonic probe having a capacitive ultrasonic transducer, and the ultrasonic probe is detachably connected to the ultrasonic transducer from the capacitive ultrasonic transducer. An ultrasonic wave having a transmission circuit that generates an ultrasonic transmission signal for transmitting the ultrasonic wave, and a reception circuit that performs signal processing on the ultrasonic wave reception signal generated by receiving the ultrasonic wave by the capacitive ultrasonic transducer An ultrasonic transducer for transmission composed of an observation device, a plurality of transmission capacitive cells that transmit the ultrasonic waves, and the reflected ultrasonic wave of the transmitted ultrasonic waves Receiving ultrasonic transducers composed of a plurality of reception capacitive cells that receive ultrasonic waves and output ultrasonic reception signals, and between the transmission ultrasonic transducer and the transmission circuit of the ultrasonic observation device A transmission signal cable for connecting the It is transmitted by the reception signal cable connecting the trusted ultrasonic transducer and the reception circuit of the ultrasonic observation apparatus, and the ultrasonic transmission signal and the reception signal cable transmitted by the transmission signal cable. First and second matching sections for matching electrical impedance with respect to the ultrasonic reception signal, respectively, and the capacitive ultrasonic transducer has one pixel for the plurality of transmission capacitive cells. An ultrasonic beam for one pixel is obtained by arranging in a predetermined transmission area set as a transmission area for transmitting an ultrasonic wave for generating an ultrasonic beam for one minute, and the plurality of reception capacitive cells Therefore, the first matching unit and the second matching unit are configured to be arranged in a predetermined reception area set as a reception area for receiving reflected ultrasonic waves transmitted from the predetermined transmission area. If part, Ru provided in the predetermined receiving each region and the predetermined transmission area.

Claims (20)

An ultrasonic probe having a capacitive ultrasonic transducer;
The ultrasonic probe is detachably connected, a transmission circuit that generates an ultrasonic transmission signal for transmitting ultrasonic waves from the capacitive ultrasonic transducer, and an ultrasonic transducer by the capacitive ultrasonic transducer An ultrasonic observation apparatus having a reception circuit that performs signal processing on an ultrasonic reception signal generated by receiving a sound wave;
The capacitive ultrasonic transducer is configured to receive a transmission ultrasonic transducer including a plurality of transmission capacitive cells that transmit ultrasonic waves and a reflected ultrasonic wave of the transmitted ultrasonic waves. A receiving ultrasonic transducer composed of a plurality of receiving capacitive cells that output ultrasonic reception signals;
A transmission signal cable for connecting between the transmission ultrasonic transducer and a transmission circuit of the ultrasonic observation device;
A reception signal cable connecting between the reception ultrasonic transducer and the reception circuit of the ultrasonic observation device;
First and second matching sections for matching electrical impedance with respect to the ultrasonic transmission signal transmitted by the transmission signal cable and the ultrasonic reception signal transmitted by the reception signal cable, respectively;
An ultrasonic diagnostic apparatus comprising:   2. The ultrasonic diagnosis according to claim 1, wherein the second matching unit is provided in the vicinity of an output side end of the reception signal cable and an input end of the reception circuit in the ultrasonic observation apparatus. apparatus.   2. The super matching unit according to claim 1, wherein the first matching unit is provided in the vicinity of an input side end of the transmission signal cable and an output end of the transmission circuit in the ultrasonic observation apparatus. Ultrasonic diagnostic equipment.   The supermarket according to claim 2, wherein the first matching unit is provided in the vicinity of an input side end of the transmission signal cable and an output end of the transmission circuit in the ultrasonic observation apparatus. Ultrasonic diagnostic equipment.   2. The ultrasonic diagnostic apparatus according to claim 1, wherein the second matching unit is provided in the vicinity of the reception ultrasonic transducer and an input side end of the reception signal cable.   2. The ultrasonic diagnostic apparatus according to claim 1, wherein the first matching unit is provided in the vicinity of the transmission ultrasonic transducer and an output side end of the transmission signal cable.   The ultrasonic diagnostic apparatus according to claim 6, wherein the second matching unit is provided in the vicinity of the reception ultrasonic transducer and an input side end of the reception signal cable.   The first matching unit includes a third matching unit provided in the vicinity of the transmission ultrasonic transducer and an output side end of the transmission signal cable, and an input side end of the transmission signal cable. 2. The ultrasonic diagnostic apparatus according to claim 1, further comprising: a fourth matching unit provided in the vicinity of the output terminal of the transmission circuit.   The second matching unit includes a fifth matching unit provided in the vicinity of the reception ultrasonic transducer and an input side end of the reception signal cable, and an output side end of the reception signal cable. The ultrasonic diagnostic apparatus according to claim 1, further comprising: a sixth matching unit provided in the vicinity of the input terminal of the receiving circuit.   2. The ultrasonic diagnostic apparatus according to claim 1, wherein characteristic impedance values of the transmission signal cable and the reception signal cable are the same.   2. The ultrasonic diagnostic apparatus according to claim 1, wherein characteristic impedance values of the transmission signal cable and the reception signal cable are different.   The capacitive ultrasonic transducer is arranged in a predetermined transmission area set as a transmission area for transmitting an ultrasonic wave for generating an ultrasonic beam for one pixel of the plurality of transmission capacitive cells. In addition, the plurality of reception capacitive cells are set as reception areas for receiving reflected ultrasonic waves of ultrasonic waves transmitted from the predetermined transmission area in order to acquire an ultrasonic beam for one pixel. 8. The configuration according to claim 7, wherein the first matching unit and the second matching unit are provided for each of the predetermined transmission region and the predetermined reception region. The ultrasonic diagnostic apparatus as described.   The capacitive ultrasonic transducer is arranged in a predetermined transmission area set as a transmission area for transmitting an ultrasonic wave for generating an ultrasonic beam for one pixel of the plurality of transmission capacitive cells. In addition, the plurality of reception capacitive cells are set as reception areas for receiving reflected ultrasonic waves of ultrasonic waves transmitted from the predetermined transmission area in order to acquire an ultrasonic beam for one pixel. The first matching unit and the second matching unit are provided in the vicinity of the plurality of transmission capacitance type cells and the plurality of reception capacitance type cells, respectively. The ultrasonic diagnostic apparatus according to claim 7, wherein:   The capacitive ultrasonic transducer transmits and receives ultrasonic waves for generating an ultrasonic beam for one pixel through the plurality of transmission capacitive cells and the plurality of reception capacitive cells. The first matching unit and the second matching unit are arranged in a predetermined region set as a region to be transmitted, and each of the plurality of transmission capacitance type cells and the plurality of reception electrostatic cells The ultrasonic diagnostic apparatus according to claim 7, wherein the ultrasonic diagnostic apparatus is provided in the vicinity of the capacitive cell. The ultrasonic probe is configured to mechanically connect the plurality of transmission capacitance type cells and the plurality of reception capacitance type cells attached to a distal end portion of a rotation shaft adjacent to a direction orthogonal to the axial direction of the rotation shaft. A rotational drive unit for rotationally driving
The rotation driving unit is configured to perform an ultrasonic transmission period for one pixel by the plurality of transmission capacitive cells and an ultrasonic reception period for one pixel by the plurality of reception capacitive cells. The ultrasonic diagnostic apparatus according to claim 7, further comprising a stepping motor that is rotationally driven stepwise. The first matching unit includes a first element having a predetermined impedance value and a second element that can vary the impedance value, and
The ultrasonic diagnosis according to claim 7, wherein the second matching unit includes a third element having a predetermined impedance value and a fourth element capable of changing the impedance value. apparatus.   The ultrasonic diagnostic apparatus according to claim 16, wherein each of the second element and the fourth element includes a trimmer capacitor whose capacitance value can be varied. The ultrasonic probe includes a plurality of N transmission capacitance type cells and a plurality of N reception capacitance type cells arranged in a circumferential direction of a distal end portion of an elongated insertion portion. Sequentially, it has an electronic scanning capacitive ultrasonic transducer that is electrically selected and operated for transmission and reception by M (<N) units,
The first matching unit performs matching of electrical impedance when transmitting the ultrasonic transmission signal from the transmission signal cable to the M transmission capacitance type cells,
The said 2nd matching part performs the matching of the electrical impedance at the time of transmitting the said ultrasonic reception signal to the said cable for reception signals from the said M pieces of receiving electrostatic capacitance type | mold cells. The ultrasonic diagnostic apparatus as described. The first matching unit includes a first element having a predetermined impedance value and a second element that can vary the impedance value, and
The ultrasonic diagnosis according to claim 18, wherein the second matching unit includes a third element having a predetermined impedance value and a fourth element capable of changing the impedance value. apparatus. Further, the reference waveform of the ultrasonic wave reception signal acquired by setting the first and second matching portions to the matching state with respect to the reference reference ultrasonic object, and the allowable boundary from the reference waveform A storage unit that stores in advance information on a reference and threshold signal level at least at a representative distance in the threshold waveform acquired when mismatching is performed;
From the comparison between the signal level of the ultrasonic reception signal obtained when transmitting / receiving ultrasonic waves to / from the reference ultrasonic object and the reference and threshold signal levels read from the storage unit, the first and the first A determination unit that determines whether the two matching units are in a matching state;
The ultrasonic diagnostic apparatus according to claim 7, further comprising:

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